Methods and systems for controlled deployment of needle structures in tissue

ABSTRACT

A system for deploying needles in tissue includes a controller and a visual display. A treatment probe has both a needle and tines deployable from the needle which may be advanced into the tissue. The treatment probe also has adjustable stops which control the deployed positions of both the needle and the tines. The adjustable stops are coupled to the controller so that the virtual treatment and safety boundaries resulting from the treatment can be presented on the visual display prior to actual deployment of the system.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of Provisional Application No.61/698,196, filed Sep. 7, 2012, the full disclosure of which isincorporated herein by reference.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates generally to medical methods andapparatus. More particularly, the present invention relates to methodsand systems for controlling the deployment of needles using treatmentand safety boundaries projected onto an image of tissue to be treated.

Current medical treatments of organs and tissues within a patient's bodyoften use a needle or other elongate body for delivery of energy,therapeutic agents or the like. Optionally the methods use ultrasoundimaging to observe and identify a treatment target and track theposition of the needle relative to the treatment target.

Of particular interest to the present invention, a treatment for uterinefibroids has recently been proposed which relies on the transvaginal orlaparoscopic positioning of a treatment device in the patient's uterus.A radiofrequency or other energy or therapeutic delivery needle isdeployed from the device into the fibroid, and energy and/or therapeuticsubstances are delivered in order to ablate or treat the fibroid. Tofacilitate locating the fibroids and positioning the needles within thefibroids, the device includes an ultrasonic imaging array with anadjustable field of view in a generally forward or lateral directionrelative to an axial shaft which carries the needle. The needle isadvanced from the shaft and across the field of view so that the needlecan be visualized and directed into the tissue and the targeted fibroid.

While effective and very beneficial for patients, such needle ablationand treatment protocols face several challenges. First, initialdeployment of the needle can be difficult, particularly for physicianswho have less experience. While the physician can view the tissue andtarget anatomy in real time on an imaging screen, it can be difficult toprecisely predict the path the needle will take and assess its finaltreatment position. While the needle can certainly be partially or fullyretracted and redeployed, it would be advantageous to minimize thenumber of deployments required before treatment is effected.

A second challenge comes after the needle has been deployed. While theposition of the needle can be observed on the ultrasonic or other visualimage, the treatment volume resulting from energy or other therapeuticdelivery can be difficult to predict. As with initial positioning,experience will help but it would be desirable to reduce the need toexercise judgment and conjecture.

A third challenge lies in assuring that nearby sensitive tissuestructures, such as the serosa surrounding the myometrium, are notunintentionally damaged. As with judging the treatment volume,predicting the safety margin of the treatment can be difficult.

U.S. Pat. No. 8,088,072, commonly assigned with the present application,describes a system for projecting safety and treatment boundaries on areal time image of the fibroid or other tissue structure to be treated.While very effective when used with single needles, the system of the'072 patent is not optimized for use with multiple needle/tineassemblies, such as those taught in commonly owned U.S. Pat. Nos.8,206,300 and 8,262,574.

For these reasons, it would be desirable to provide improved systems andmethods for the deployment of energy delivery and other needles withinultrasonic or other imaging fields of view in energy delivery or othertherapeutic protocols. It would be particularly useful to provide thetreating physician with information which would assist in initialdeployment of a plurality of needles or tines in order to improve thelikelihood that the needle assembly will be properly positioned relativeto a targeted anatomy to be treated. It would also be desirable toprovide feedback to the physician to assist in accurately predicting atreatment volume. Such information should allow the physician, ifnecessary, to reposition the probe in order to increase the likelihoodof fully treating the anatomy. Furthermore, it would be desirable toprovide feedback to the physician allowing the physician to assess asafety margin so that sensitive tissue structures are not damaged. Allsuch feedback or other information are preferably provided visually onthe ultrasonic or other imaging screen so that the needle position canbe quickly predicted, assessed, and treatment initiated. It would befurther desirable if the feedback information were presented on adisplay screen in response to manipulating the probe while minimizingthe need to enter data or commands onto a system controller or display,and still further desirable if such manipulation of the probe could setstops or other limits which controlled the extent of subsequent needledeployment. At least some of these objectives will be met by theinventions described hereinafter.

2. Description of the Background Art

U.S. Pat. Nos. 8,088,072; 8,206,300 and 8,262,574 have been describedabove and are incorporated herein by reference. U.S. Pat. No. 7,918,795,commonly assigned with the present application, describes probes usefulfor both imaging and treating uterine fibroids, which probes could beused in the systems and methods of the present application and isincorporated herein by reference. Other commonly assigned patents andpublished applications describing probes useful for treating uterinefibroids in the systems include U.S. Pat. Nos. 7,874,986 and 7,815,571;and U.S. Patent Publications 2007/0179380 and 2008/0033493. See alsoU.S. Pat. No. 6,050,992 and U.S. patent Publication 2007/0006215.

BRIEF SUMMARY OF THE INVENTION

The present invention provides methods and systems for deploying needlestructures in tissue. The needle structures may in some cases comprise asingle needle but in most cases will comprise multiple needles or needleand tine assemblies as described in more detail below. The needlestructures are usually intended to deliver a therapy to the tissue, mosttypically being configured to deliver radiofrequency energy, plasmaenergy, therapeutic ultrasound energy, microwave energy, heat, cold(cryogenic treatment), or other energy to ablate or otherwise modify atarget tissue or targeted anatomy within the tissue. Alternatively, theneedle structures could also provide drug or other substance delivery,morcellation, or other tissue treatments which can be effected using aneedle structure.

The methods and systems of the present invention are particularlysuitable for treating fibroids in a patient's uterus where a probecarrying the needle structure and an imaging transducer, typically anultrasonic imaging transducer, is introduced transvaginally andtranscervically into the uterus, or in other cases laparoscopically intoand through an exterior of the uterus or other organ or tissue target.The probe is manipulated within the uterus to deliver ablative energy tothe fibroid as described in more detail below. In most embodiments ofthe present invention, the needle structure is “virtually” deployed on areal-time image of the tissue prior to actual deployment of the needlein the actual tissue. Treatment and/or safety boundaries within thetissue will also be determined and optionally adjusted prior to theactual deployment of the needle structure. In other embodiments, theactual position of the needle structure may be tracked and thecorresponding treatment and/or safety boundaries projected on the screenin real time. In all embodiments, the treatment and safety boundariescan be checked before treatment is commenced.

The methods and systems of the present invention further provide that,once the parameters of the virtual deployment have been selected usingthe virtual images, the needle structure is actually deployed in thereal tissue at a location and/or in a pattern which matches the virtualdeployment configuration. In a first exemplary embodiment, suchdeployment is achieved by manipulating “stops” or other mechanicalelements on the probe during the virtual deployment on the real-timeimage. The stop positions correspond to actual needle deploymentpositions (the stops typically act as limits which allow the needlestructure to be deployed to a specific location and in a specificpattern), and the system calculates the treatment and/or safetyboundaries based on the stop positions as well as on energy deliverydata which is supplied to or generated by a system controller. Thissystem may alternatively or additionally track the position of thetreatment probe and/or needle structure in the uterus, thus allowing thetreatment and safety boundaries which are projected upon the real-timeimage of the tissue to be calculated and/or updated as the probe ismoved and the needle structure advanced by the treating physician. Inthe first exemplary embodiment, once the treatment region and/or safetyboundary are properly positioned on the real-time image relative to theanatomy to be treated, the physician may hold the probe in place anddeploy the needle structure until it reaches its “stop” position(s)which have been preset into the probe during the initial imaging andset-up phase of the treatment. In some cases, the stops can beautomatically set as the physician manipulates the treatment and/orsafety boundary on the screen using the controls on the treatment probe.In alternative embodiments, the physician may manipulate the probe andadvance the needle structure while viewing the safety and/or treatmentboundaries in real time without having previewed the virtualprojections.

In the exemplary embodiments, at least one main or central needle willbe deployed from the treatment probe, and a plurality of tines orsecondary needles will be deployed from the main or central needle(s).Most often, there will be a single main needle which is deployeddistally from a shaft of the probe along a central axis thereof. Aplurality of tines will then be advanced from the single needle in adistally diverging pattern. In other embodiments, a plurality of needlesor tines may be advanced from the probe without use of a main or centralneedle. In such cases, the needles or tines will typically expand ordiverge into a three-dimensional array as they are advanced distally.

Exemplary anatomical features that may be imaged and subsequentlytreated include fibroids, tumors, encapsulated tissue masses,pseudoencapsulated tissue masses, and the like. Of particular interestof the present invention, the probe may be positioned in the uterus andthe needle structure deployed to a location proximate to or within afibroid located in the myometrium tissue of the uterus. In such cases,it will be desirable to also image the serosa which surrounds themyometrium and/or other sensitive anatomical features that could bedamaged by the energy-mediated treatments described herein.

As used herein, a treatment region is defined by a treatment boundarywhich is calculated by the system controller based upon the needlestructure deployment configuration (either as set by the “stops” or ascalculated in real-time as the needle structure is deployed) and theenergy delivery parameters set by or input into the system controller.Energy or other therapy delivered by the needle structure deployed inthe selected pattern at the selected location will effectively treat thetarget tissue to achieve ablation or other therapeutic results. Asdescribed below, it will thus be desirable to manipulate the probe aswell as the needle structure stop(s) and/or actual needle structure sothat the treatment region at least partially surrounds the anatomy to betreated as seen on the real-time image display of the system.

As further used herein, the safety region is defined by a safetyboundary which is calculated by the system. As with the treatmentregion, the safety boundary is calculated based upon the needlestructure “stops” and/or actual needle structure positions which havebeen set or adjusted on the treatment probe by the physician as well asthe energy delivery parameters which are input into or set by the systemcontroller. The safety boundary will differ from the treatment boundaryin that the safety boundary will be set at a minimum threshold distancebeyond the boundary of the tissue treatment region where the risk ofdamaging tissue is reduced or eliminated entirely.

In a first aspect of the present invention, methods for deploying aneedle structure in tissue comprise positioning a treatment probe havinga deployable needle structure near a surface of the tissue to betreated, for example, adjacent to a uterine wall over the myometrium ofa uterus. A real-time image of the tissue is provided, typically usingan imaging transducer such as an ultrasonic array which is carried bythe treatment probe, and projected onto a display connected to acontroller. The real-time image includes an anatomical feature to betreated, such as a fibroid. At least one of a treatment region and asafety region is projected onto the real-time image prior to deployingthe needle structure. A size and/or a position of a boundary of thetreatment region and/or the safety region is then adjusted on thereal-time image still prior to deploying the needle structure. After theboundary(ies) of the treatment region and/or the safety region areproperly positioned on the real-time image relative to the anatomy to betreated, the needle structure may be deployed from the probe into thetissue to provide treatment within the projected treatment/safetyboundary after the boundary has been adjusted.

The boundary of the treatment region and/or safety region can be movedor adjusted in several ways. First, manual movement of the probe by thephysician will cause the real time image of the tissue and anatomyprojected on the screen to move relative to the treatment/safetyboundary(ies) projected on the screen. Since the position(s) of thetreatment and/or safety boundary projected on the screen depends on thecalculated position of the needle structure, it will be appreciated thatmovement of the probe itself will cause the calculated needle positionto move within the real-time image. In addition to such gross movementof the treatment probe in the uterus, the position of the treatment orsafety region projected on the real-time image can be adjusted bycontrols on the probe, e.g. by manually positioning a needle stopelement provided on the probe. The needle stop element provides aphysical limit on deploying at least one needle of the needle structureso that when the needle is actually deployed in tissue, the needle willbe precisely located at the position determined by the needle stop.Prior to deployment, the position of the needle stop itself is trackedby the system controller and used to calculate the position(s) of thetreatment and/or safety boundaries.

In specific embodiments, one or more sensor(s) on the probe track(s)movement of the stop(s) in order to reposition and/or resize theprojected boundaries. For example, a rotary sensor could be provided onthe targeting knob so that when the knob is rotated, the treatmentregion grows and shrinks and a gear train turns a lead screw which movesthe stop. Thus, sensors coupled to the stops track the projectedsafety/treatment boundary.

Alternatively, in other embodiments, the position(s) and size(s) of thetreatment and/or safety boundaries may be adjusted on the controllerand/or display screen using an appropriate interface, such as akeyboard, joy stick, mouse, touch panel, touch screen, or the like. Oncethe treatment and/or safety boundaries are properly (virtually)positioned on the screen, the controller can control the deployment ofthe needle structure on the treatment probe. For example, the controllercould position servo motors on the probe to position the needle/tinestops or could directly position the needles/tines without the use ofstop structures.

In addition to the needle stop, the probe will usually also have a tinestop which determines the extent to which a plurality of tines may beadvanced from the needle. While the present disclosure generally refersto a single tine stop, other embodiments may employ multiple tine stops,and the individual tines may be individually controlled or be controlledin groups of less than the whole. The tine stop will be configured to bemonitored by the system controller so that the controller can calculatethe size of the treatment or safety boundary as the tine stop isadjusted. Additionally, once the desired position and size of thetreatment and/or safety boundaries are determined, the tine stop willact to limit the travel of the tines so that they are physicallydeployed in a pattern which provides treatment within the desiredtreatment/safety boundaries when energy is delivered through the needlestructure.

Once the needle stop and tine stop have been set, and the needlestructure has been advanced in tissue to the limits defined by thestops, energy may be delivered through the needle structure to treat thetissue. The energy, of course, will be delivered at a treatment powerand/or treatment time which has been used to calculate the treatmentregion and/or safety region boundaries. In some embodiments, it will bepossible for the controller to adjust the position or size of thetreatment or safety boundaries based on the power, time and/or othertreatment parameters (in addition to needle/tine position) which havebeen selected by the physician. In this way, both the needle/tinepositions and the power and time of energy delivery are taken intoaccount to calculate the position or size of the treatment or safetyboundaries. Alternatively, drug delivery, tissue morcellation, and othertherapies could be delivered through the deployed needle structure.

Optionally, virtual needle location information can be projected ontothe real-time image while the position and/or size of the treatmentand/or safety boundaries are being adjusted. For example, the needlelocation information could comprise a plurality of fiducials or markerswhich are projected onto the real-time image to indicate the projectedpositions of the needle tip(s), or other needle position information. Inother cases, it would be possible to project complete images of theneedle lengths as they would travel through the tissue (but prior toactual deployment). The needle location information would, of course,preferably be updated as the probe stops are being adjusted and wouldallow the physician to see where the needle will be after needledeployment.

In another aspect of the present invention, a system for treating ananatomical feature in tissue comprises a real-time image display, atreatment probe, and a positionable stop structure on the treatmentprobe. The treatment probe carries a deployable needle structure and animaging transducer, wherein the transducer is connectable to thereal-time image display. The position stop structure on the probe (1)controls at least one of a position or size of a treatment or safetyregion projected on the real-time image display and (2) physicallylimits deployment of the needle structure so that subsequent treatmentof the tissue is within the treatment and/or safety region.

An exemplary needle structure comprises a needle and a plurality oftines which may be advanced from the needle. The tines assume a distallydiverging pattern as they are advanced from the needle, and the stopstructure typically comprises a needle stop element and a separate tinestop element. The needle stop element at least partially controls theposition of the treatment or safety region projected on the real-timeimage display and the tine stop element at least partially controls thesize of the treatment or safety region projected on the real-time imagedisplay.

The treatment systems may optionally further comprise a controllerconnectable to the probe for delivering energy to the needle structure,where the system is configured to control the projected treatment sizeor projected safety region size based upon both an energy level to bedelivered by the controller and the position of the stop element(s)which may be tracked by sensors on the treatment probe

In a further aspect of the present invention, an imaging and therapeuticdelivery system comprises an imaging component comprising an imagingshaft having a proximal end, a distal end, and an imaging transducer atthe distal end. A needle component comprising a needle shaft having adistal end and a proximal end and a needle structure reciprocallydisposed on or within the shaft is configured to removably attach to theimaging shaft with the shafts lying side-by-side with their respectiveaxes in parallel.

In specific examples, the imaging transducer on the imaging shaft ispivotally attached at the distal end of the imaging shaft, and thedistal end of the needle shaft is disposed proximally of the pivotallyattached imaging transducer when the needle shaft is attached to theimaging shaft. The needle structure in the needle shaft typicallyreciprocates distally along the axis of the needle shaft, and theimaging transducer pivots away from the axis of the needle shaft whenthe needle shaft is attached to the imaging shaft. The imaging componentmay further comprise an imaging handle section attached to a proximalend of the imaging shaft, and the needle component may further comprisea needle handle section attached to a proximal end of the needle shaft.In such embodiments, the imaging handle section and needle handlesection will typically form a complete handle when the needle shaft isattached to the imaging shaft. The imaging handle section usually has aninterior which holds circuitry configured to connect the imagingtransducer with an external imaging display and the needle handlesection including mechanisms for advancing the tine needle structure,and the imaging handle section usually further comprises mechanisms forpivoting the imaging transducer relative to the imaging shaft.

In a still further aspect of the present invention, a method fordeploying a plurality of tines from a needle in tissue comprisesproviding a real-time image of the tissue, including an anatomicalfeature to be treated, on a display. The needle is penetrated intotissue proximate the anatomical feature, typically in a distaldirection, and tines are deployed from the needle further into thetissue. As with previous embodiments, the tines typically divergeradially as they are advanced distally from the needle to increase thevolume of tissue to be treated. At least one of a treatment boundary anda safety boundary are projected onto the display in response to the tinedeployment. An extent of the tine deployment can be adjusted to changethe size and/or shape of the treatment and/or safety boundary which isprojected on the display. In contrast to prior embodiments, thephysician is able to position the needle and tines without havingpreviously virtually projected the safety and/or treatment boundariesonto the image of the anatomy. Instead, the actual needle and tinedeployment can be relied on to position and reposition the safety and/ortreatment boundaries on the real time image until the physician issatisfied that a subsequent treatment will be both safe and effectiveusing the actually deployed needle and tine configuration. In additionto the actual needle and tine deployment, of course, the projectedtreatment and/or safety boundaries will also depend on the intendedpower and time lengths of the treatment in a manner analogous to theprojections of the virtual boundaries discussed previously. After anacceptable size and/or safety boundary has been achieved, the treatmentmay be delivered through the tines. In particular embodiments,deployment of the tines may be tracked via sensors in a needle/tinedeployment mechanism on a probe used to deploy the needle and tines. Insuch cases, penetrating the needle will comprise advancing the needlefrom the probe which has been penetrated into the tissue. Usually, theextent of needle deployment from the probe will also be relied on indetermining the projected safety and/or treatment boundaries on thedisplay.

In still further aspects of the present invention, a system for treatingan anatomical feature in tissue comprises a real-time display connectedto a controller. The system projects and adjusts a size of at least oneof a treatment boundary and a safety boundary onto the display. Atreatment probe having a deployable needle structure and an imagingtransducer is provided which is connectable to the controller and thedisplay. The treatment probe carries at least one servo drive motorwhich is connected to and driven by the controller. The controller isconfigured to drive the servo motor to position the needle structure toprovide a treatment which is effective over the region defined by thetreatment boundary and which does not extend significantly beyond thesafety boundary.

In specific embodiments of the system, the needle structure may comprisea needle and a plurality of tines advanceable from the needle in adistally diverging pattern. The at least one servo motor may comprise afirst servo motor which drives the needle and a second servo motor whichdrives the plurality of tines. The system usually comprises a userinterface configured to allow the user to virtually adjust the sizeand/or a position of the treatment and/or safety boundary on thedisplay. In some instances, as described previously, an interface may beon the treatment probe itself. In other cases, the interface maycomprise a more conventional keyboard, mouse, roller ball, touch screen,voice activation, or the like which is connected to the controller toallow the user to virtually position the needle structure prior toactually positioning the needle structure. In still other embodiments,the treatment probe may comprise servo motors for positioning the needlestructure and/or sensors for detecting the extent to which the needlestructure has been deployed. In such cases, the user may position theneedle structure using the servos (without having generated a virtualprojection of the safety and/or treatment boundaries), and observe theprojected safety and/or treatment boundaries as they are calculated andprojected by the system controller. In all cases, the system can be usedto deliver energy or other treatments only after the deployment of theneedle structure has been confirmed to meet the requirements of thesafety and/or treatment boundaries.

All publications, patents, and patent applications mentioned in thisspecification are herein incorporated by reference to the same extent asif each individual publication, patent, or patent application wasspecifically and individually indicated to be incorporated by reference.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic illustration of the system of the presentinvention comprising a system controller, an image display, and atreatment probe having a deployable needle structure and imagingtransducer.

FIG. 2 is a perspective view of the treatment probe of the presentinvention.

FIG. 3 is a view of the treatment probe of FIG. 2 illustrating animaging component of the probe separated from a needle component withportions broken away and portions enlarged.

FIG. 3A illustrates a distal end of the needle component being connectedto a distal end of the imaging component.

FIGS. 4A through 4F illustrate the internal mechanisms of the needledeployment component of the probe, including a needle stop housing and aneedle carriage, showing how the mechanisms are manipulated in order todeploy the needle structure.

FIGS. 5A and 5B illustrate an interlock mechanism which preventsdeployment of the needle structure prior to deflection of an imagingarray on the imaging component of the probe.

FIGS. 6A and 6B illustrate a gear train mounted on the needle stophousing used to deploy a needle and a plurality of tines of the needlestructure.

FIGS. 6C and 6D illustrate details of the needle carriage.

FIGS. 7A through 7C show relative movement of the needle carriage andneedle stop housing.

FIG. 8 is a bottom view of the needle carriage.

FIG. 9 illustrates a distal portion of the treatment probe introducedinto a uterine cavity to image a fibroid in the myometrium.

FIGS. 10A-15A illustrate “screenshots” of the real-time image display asthe treatment and safety boundaries are being adjusted using thetreatment probe in accordance with the principles of the presentinvention.

FIGS. 10B-15B illustrate manipulation of the handle which corresponds tothe repositioning of the projected images of the treatment and safetyboundaries on the real-time images of FIGS. 10A-15A.

FIGS. 16A-16D illustrate the provision of fiducials or markers on thereal-time image, where the fiducials or markers correspond to needle tiplocations.

FIG. 17A-17C illustrate an alternative construction of the needlehousing of the present invention having sensors for detecting thepositions of the needle carriage and the tine slide as they arepositioned to deploy the needle and tines, respectively.

FIGS. 18A and 18B illustrate a further alternative embodiment of theneedle housing of the present invention employing servo motors and drivescrews for positioning both the needle carriage and the tine slide.

FIG. 19 illustrates a system diagram where real-time ultrasound imagedata is relied on to determine the positions of the needle structures ofthe present invention.

FIG. 20 illustrates a system diagram where external needle tracking datais used for tracking the needle position.

DETAILED DESCRIPTION OF THE INVENTION

As illustrated in FIG. 1, a system 10 constructed in accordance with theprinciples of the present invention includes a system controller 12, animaging display 14, and a treatment probe 16. The system controller 12will typically be a microprocessor-based controller which allows bothtreatment parameters and imaging parameters to be set in a conventionalmanner. The display 14 will usually be included in a common enclosure 18together with the controller 12, but could be provided in a separateenclosure. The treatment probe 16 includes an imaging transducer 20which is connected to the controller 12 by an imaging cord 24. Thecontroller 12 supplies power to the treatment probe via a treatment cord22. The controller 12 will typically further include an interface forthe treating physician to input information to the controller, such as akeyboard, touch screen, control panel or the like. Optionally, a touchpanel may be part of the imaging display 14. The energy delivered to thetreatment probe by the controller may be radiofrequency (RF) energy,microwave energy, a treatment plasma, heat, cold (cryogenic therapy), orany other conventional energy-mediated treatment modality. Alternativelyor additionally, the treatment probe could be adapted to deliver drugsor other therapeutic agents to the tissue anatomy to be treated. In someembodiments, probe 16 plugs into an ultrasound system and into aseparate radio frequency (RF) generator. An interface line connects theultrasound system and the RF generator.

Referring now to FIGS. 2 and 3, the treatment probe 16 comprises aneedle component 26 and an imaging component 28. The needle componentand imaging component are constructed as separate units or assemblieswhich may be removably attached to each other for use. After use, theneedle component may be separated and will typically be discarded whilethe imaging component will be sterilized for reuse. The treatment probe16 is shown in its fully assembled configuration in FIG. 2 and is shownin its disassembled configuration in FIG. 3. In other embodiments of thepresent invention, the needle component and the imaging component couldbe combined in a single, integrated handle unit.

The needle component 26 comprises a handle portion 27 having a slidablymounted targeting knob 30 on its upper surface. The targeting knob 30controls the positioning of internal stops within the handle which aremonitored by the controller 12 (FIG. 1) in order to calculate the sizeand position of the boundaries of the targeting region and/or the safetyregion which are shown on the display 14. The stops will also serve tophysically limit deployment of the needle 56 and optionally tines 57, aswill be described in more detail below.

The needle 56 is deployed from the needle shaft 34, and the needle andoptional tines together form a needle structure which may beconstructed, for example, as previously described in commonly owned U.S.Pat. Nos. 8,206,300 and 8,262,574, the full disclosures of which areincorporated herein by reference.

The handle portion 27 of the needle component 26 further includes afluid injection port 32 which allows saline or other fluids to beinjected through the needle shaft 34 into a target region in the tissuebeing treated, such as the uterus. The needle handle 27 also includes aneedle slide 36, a needle release 38, and a tine slide 40 which are usedto deploy the needle 56 and tines 57, as will be described in moredetail below. The imaging cord 24 is attachable at a proximal end of thehandle portion 27 of the imaging component 28 for connection to thecontroller 12, as previously described.

The imaging component 28 comprises a handle portion 29 and an imagingshaft 44. A deflection lever 46 on the handle portion 29 can beretracted in order to downwardly deflect the imaging transducer 20, asshown in broken line in FIG. 3. A needle component release lever 48 iscoupled to a pair of latches 50 which engage hooks 52 on a bottomsurface of the handle portion 27 of the needle component 26. The needlecomponent 26 may be releasably attached to the imaging component 28 byfirst capturing a pair of wings 58 (only one of which is shown in FIG.3) on the needle shaft 34 beneath hooks 60 on the imaging shaft 44, asshown in FIG. 3A. A bottom surface of the needle handle portion 27 maythen be brought down over an upper surface of the imaging handle portion29 so that the hooks 52 engage the latches 50 to form a completeassembly of the treatment probe 16, where the handle portions togetherform a complete handle, for use in a procedure. After use, the needlecomponent release lever 48 may be pulled in order to release the hooks52 from the latches 50, allowing the handle portions 27 and 29 to beseparated.

In use, as will be described in more detail below, the targeting knob 30is used to both position (translate) and adjust the size of a virtualtreatment region which is projected onto the display 14 of the system10. The knob 30 may be moved distally and proximally in a slot on anupper surface of the handle portion 27 in order to translate theposition of the treatment/safety region on the image, and the knob mayalso be rotated in order to adjust the size of the boundary of thetreatment/safety region. Sliding and rotating the knob 30 will alsoadjust the position of mechanical stops in the handle portion 27 whichlimit the deployment of the needle 56 and tines 57 so that, once thevirtual boundaries of the treatment/safety region have been selected onthe real-time image, the needle and tines may be automatically advancedto the corresponding deployment positions by moving the needle slide 36and tine slide 40 until their movement is arrested by the stops. Theposition of the treatment/safety region is also dependent on thelocation at which the physician holds the treatment probe 16 within thetarget tissue. Thus, advancement of the needle and tines using theslides 36 and 40 will result in the proper placement of the needle andtines within the target tissue only if the treatment probe position isheld steady from the time the stops are set until advancement of theneedle/tines is completed. In preferred embodiments, rotating the knob30 will also determine the length of and/or power delivery during atreatment protocol. Thus, the knob may be used to virtually size thetreatment/safety region based not only on the degree to which the tineshave been advanced, but also the amount of energy which is beingdelivered to the target tissue.

Referring now to FIGS. 4A through 4F, construction of the needle handleportion 27 and internal components thereof will be described in greaterdetail. Note that the orientation of the needle component 26 is reversedrelative to that shown in FIGS. 2 and 3 so that the needle shaft 34 isextending to the right in FIGS. 4A-4F rather than to the left as shownin FIGS. 2 and 3. The handle portion 27 of the needle component 26 isshown with its upper portion partially removed in each of FIGS. 4Athrough 4F. A needle stop housing 64 is slidably mounted in the housingwith a shaft 31 of knob 30 traveling in a slot 33 (FIG. 2) as thehousing 64 is translated.

A needle carriage 68 is also slidably mounted in the housing portion 27and carries a tine stop 66 which is mounted on a lead screw 72. The knob30 is coupled to the lead screw 72 by a gear train 71 which turns adrive shaft 70 which is slidably inserted into the lead screw 72. Thedrive shaft 70 will have an asymmetric cross-section which slides intoand out of a mating passage axially aligned in the lead screw 72. Thus,the knob 30 can be used to rotate the lead screw independent of therelative axial positions of the needle stop housing 64 and the needlecarriage 68.

As will be explained in more detail below, treatment probe 16 has anumber of interlock features which prevent unintentional actuation ofthe stops, needle, and tines as well as requiring that the stoppositions and needle/tine actuations be performed in a proper order. Aspart of this interlock system, pawls 74 are provided on a side of theneedle stop housing 64 such that the pawls 74 engage with a rack ofteeth 132 (FIG. 8) on the inside of the handle portion 27 housing toprevent motion of the needle stop housing 64 unless the pawls aredisengaged. The pawls are disengaged by depressing the knob 30 whichallows the knob to be moved distally and proximally on the handleportion 27 in order to reposition the needle stop housing 64 in thehousing portion 27. When the knob is released, the pawls 74 re-engage,locking the needle stop housing 64 in place relative to the handleportion 27.

Similarly, pawls 76 (FIGS. 4A and 4B) are provided on the needlecarriage 68. These pawls also engage a rack of teeth 134 (FIG. 8) on theinside of the housing of handle portion 27. The pawls 76 are normallyengaged, locking the carriage 68 in place, but may be disengaged bypressing on the T-shaped release 38, allowing the carriage to be pushedforward in order to distally advance the needle 56 which has a proximalend (not shown) carried by the carriage. The tines 57 are advanced fromthe needle 56 by the tine slide 40, as will be described below.

As shown in FIG. 4B, the positions of the needle stop housing 64 and thetine stop 66 are sensed by the needle position sensor 78 and the tineposition sensor 80, respectively. These sensors are typically rheostatswith a change of position resulting in a change of resistance which issensed by the controller 12, but other absolute position feedbackdevices, such as. LVDT, quadrature encoders or the like could also beused. Thus, prior to deployment of the needle or tines, the positions ofthe needle stop housing 64 and tine stop 66 may be tracked in real timeby the controller 12 and the calculated treatment and/or safetyboundaries displayed on the display unit 14 as the position of theneedle stop housing is adjusted and the knob 30 rotated to adjust theposition of the tine stop. Of course, the actual positions of the stopscould also be visually or numerically shown on the display 14. Prior toany actual deployment of the needle and tines, the physician will havevisual information confirming the treatment/safety region boundarieswhich will result from the needle/tine deployment which has been setinto the treatment probe by adjusting the needle and tine stops.

A particular advantage of this method and system is that the physiciancan manipulate the treatment/safety boundaries over the target anatomyby either moving the boundaries relative to (or within) the real-timeimage by manipulating (sliding and turning) knob 30 or moving the entirereal-time image with respect to the target anatomy by manipulating theentire treatment probe 16 in order to get the treatment boundary overthe tumor and keeping the safety boundary away from sensitive anatomy.So, before the physician advances any needles into the patient tissue,they can confirm in advance using the virtual targeting interface thatthe ablation will be effective and safe.

Referring to FIG. 4A, to virtually position the boundaries of thetreatment/safety regions, the targeting knob 30 may be depressed and theknob moved distally in the direction of arrow 84, reaching the positionshown in FIG. 4C. The physician will, of course, be able to move theneedle stop housing both distally and proximally so long as the knob 30is depressed, until the boundary of the treatment/safety region isproperly located as shown on the visual display 14. Once properlypositioned, the knob 30 is partially depressed to disengage rotationlock 110 (FIG. 6B), and the knob may be rotated as shown by arrow 86 toposition the tine stop 66. More specifically, rotation of knob 30rotates drive shaft 70 via the gear train 71. The drive shaft, in turn,rotates lead screw 72 which moves the tine stop 66 distally as shown byarrow 88 in FIG. 4D. Knob 30 can, of course, be rotated in eitherdirection in order to reposition the tine stop 66 distally orproximally, which repositioning causes the “virtual” boundary projectedon display 14 to expand or contract, respectively (FIG. 4D). Once theneedle stop housing 64 and the tine stop 66 are in their desiredpositions (based on the virtual or projected images of thetreatment/safety boundary on display 14), the treating physician canthen physically advance the needle and the tines to the positions presetby the needle stop housing and tine stop. Referring to FIG. 4D, theneedle release 38 is pushed in to disengage the pawls 76 and allow theneedle carriage 68 to be moved in the direction of arrow 88. The needlecarriage 68 is advanced until hitting the needle stop housing 64 asshown in FIG. 4E. Such motion of the needle carriage, in turn, distallyadvances the needle 56 as shown in broken line in FIG. 3.

After the needle 56 has been advanced, the tines 57 may be advanced bymanually pushing the tine slide 40 distally until the tine slide 40 hitsthe tine stop 66 as shown by arrow 90 in FIG. 4E. Once the slide 40 ispositioned distally, as shown in FIG. 4F, the needle 56 and tines 57will be deployed, as shown in FIG. 3. At this point the controller 12detects that the needle 56 and tines 57 have been fully extended and thephysician confirms that the ablation will be of the correct size and ata safe and effective location. The tine slide locking arm 120 releasesthe tine slide 40 when the needle carriage 68 engages the stop housing64. Thus, the switch on the tine stop 66 can be active only if the tineslide 40 was first released when the needle carriage 68 engaged the stophousing 64, with the single microswitch 112 indicating that the needle56 and the tines 57 are in their proper positions.

Referring now to FIGS. 5A and 5B, an interlock assembly for preventingmotion of the needle carriage 68 prior to deflection of the imagetransducer 20 (FIGS. 2 and 3) will be explained. The transducerdeflection lever 46 is initially pushed forwardly as shown in FIG. 5A,where the transducer 20 is in its axially aligned configuration, asshown in FIGS. 2 and 3. It will be appreciated that needle advancementwhile the transducer 20 is aligned axially would likely damage thetransducer. To avoid such damage, as it is retracted, the lever 46engages a four bar linkage 92 which is coupled to an angle lock 94 whichprevents movement of the needle carriage 68. When the lever 46 is pulledproximally, however, to deflect the transducer 20 (as shown in brokenline in FIG. 3), the four bar linkage is allowed to collapse anddisengage the angle lock 94, as shown in FIG. 5B. In this configuration,the needle carriage 68 is free to be advanced and retracted. In otherembodiments, a leveraged or pivoting beam could replace the four barlinkage.

Details of the gear train which allows the knob 30 to rotate to thedrive shaft 70 are shown in FIGS. 6A and 6B. The knob is attached tobevel gear 100 which rotates a bevel/spur combination gear 102 which inturn drives the spur gear 104 attached to the drive shaft 70. Depressingthe knob 30 retracts the pawls 74 through interaction with dowel pin 108which is moved up and down by the knob 30 and rides in slots or channelsin the pawl surfaces. A rotation lock 110 is provided and engages thebevel gear to prevent rotation of the knob. A microswitch 112 isprovided which signals to the controller when the rotation lock 110 andpawls 74 are engaged.

Referring now to FIGS. 6C and 6D, more details of the needle carriage 68will be described. FIG. 6C is a top view of the needle carriage 68,generally as shown in previous figures. FIG. 6D is a bottom view of theneedle carriage showing details not previously visible. The angle lock94 translates an arm 96 which allows or prevents the needle release 38from being actuated. As shown in FIG. 6D, the angle lock 94 is engaged(as shown in FIG. 5A). By retracting lever 46 (FIG. 5B), the angle lock94 would disengage to withdraw the arm 96 to allow the needle release 38to be depressed. The needle release 38, in turn, retracts pawls 76 whichdisengage with locking teeth 134 on handle portion 27.

A bracket 114 on the tine slide 40 engages with a shaft (not shown)which advances the tines within the needle, as will be described below.Similarly, a bracket 116 fixed to the needle carriage 68 engages aproximal end of the needle (not shown in FIG. 6D) which will advance theneedle as the carriage is advanced.

One additional lock out is shown in FIG. 6D. A spring loaded plunger 140projects out a back of tine slide 40. When the tine slide 40 is pushedup against the needle slide 36, (i.e., when the tines are not deployed),the spring loaded plunger 140 actuates the angle lock 94 and engages thearm 96 to lock out the needle release 38. When the tine slide 40 ismoved away from the needle slide 36, the plunger 140 disengages theangle lock 94 and the arm 96 unlocks the needle release 38. Of course,other lock out mechanisms could be employed. For example, the tine slide40 could engage a simple lever that directly interfaces with the needlerelease 68 without using a spring loaded plunger 140.

Referring now to FIGS. 7A through 7C, a mechanism for selectably lockingthe tine slide 40 prior to advancing the needle carriage 68 will bedescribed. A tine locking arm 120 is attached via a pivot 122 on a sideof the needle carriage 68, as shown in FIG. 7A. A side arm 124 of thelocking arm 120 is disposed to engage a bar 126 fixed to the end of theneedle stop housing 64 which engages the needle carriage when the needlecarriage is fully advanced. As the needle carriage 68 is advanceddistally (to the left in FIGS. 7A and 7B) to deploy the needle, the bar126 on needle stop housing 64 will engage the side arm 124 on the tinelocking arm 120. Such engagement will cause the locking arm to rotate ina counter-clockwise direction, thus raising a locking end 128 of the barfrom an engagement configuration (FIG. 7A) to a non-engagementconfiguration (FIG. 7B) such that the tine slide 40 may be advanceddistally only after the needle carriage has been fully advanced. In thisway, accidental, premature deployment of the tines may be prevented.

One skilled in the art will appreciate that there are many ways todesign the lock outs that control the order of deployment of thecomponents of the treatment probe. For example, the bar 126 could beintegrated into side 124 rather than 64. The lockout 120 could bedesigned as a leaf spring so that it does not rely on gravity to engagelocking end 128 with tine slide 40.

FIGS. 7B and 7C illustrate how the arm 96 of the angle lock 94 is raisedin order to lock the needle release 38 to prevent accidental needledeployment.

Referring now to FIG. 8, inner teeth 132 and 134 are formed on aninterior surface of the housing portion 27 of the needle component 26 ofthe treatment probe 16. The teeth 132 selectively engage pawls 74disposed on the needle stop housing 64, as previously described. Theteeth 134 selectively engage pawls 76 (not shown in FIG. 8) which are onthe needle carriage 68.

Referring now to FIG. 9, the system 10 of the present invention can beused to treat a fibroid F located in the myometrium M in a uterus Ubeneath a uterine wall UW (the endometrium) and surrounded by theserosal wall SW. The treatment probe 16 can be introduced transvaginallyand transcervically (or alternately laparoscopically) to the uterus, andthe imaging transducer 20 deployed to image the fibroid within a fieldof view indicated by the broken lines.

Once the fibroid is located on the display 14, as shown in FIG. 10A, thecontrols on the handle will be used to locate and size both a treatmentboundary TB and a safety boundary SB. Initially, as shown in FIG. 10A,the virtual boundary lines TB and SB are neither positioned over thefibroid nor properly sized to treat the fibroid. Prior to actual needleand tine deployment, the physician will want to both position and sizethe boundaries TB and SB for proper treatment. As the imaging transducer20 is already positioned against the uterine wall UW the only way toadvance the treatment and safety boundaries is to move the boundariesforward by depressing the targeting knob 30, as shown in FIG. 10B, andthen distally advancing the knob as shown in FIG. 11B. This will causethe treatment and safety boundaries TB and SB to move forwardly alongthe axis line AL. This causes the virtual boundaries on the real-timeimage display 14 to move over the image of the fibroid, as shown in FIG.11A.

As shown in FIG. 11A, however, the size of the treatment boundary TB isinsufficient to treat the fibroid since the boundary does not extendover the image of the fibroid. Thus, it will be necessary to enlarge thetreatment boundary TB by rotating the targeting knob 30, as shown inFIG. 12B. This enlarges both the treatment boundary TB and the safetyboundary SB, as shown in FIG. 12A. While the enlarged virtual treatmentboundary TB is now sufficient to treat the fibroid, the safety boundarySB has extended over the serosal wall SW, as also shown in FIG. 12A.Thus, there is risk that the treatment would affect more sensitivetissue surrounding the uterus, and it is necessary that the virtualsafety boundary SB be retracted by turning the targeting knob 30 in anopposite direction, as shown in FIG. 13B. This reduces the size of boththe safety and treatment boundaries SB and TB, as shown in FIG. 13A, andthe physician has confirmation that the treatment will be effectivebecause the treatment boundary TB completely surrounds the fibroid onthe real-time image display, and that the treatment will be safe becausethe safety boundary SB is located within the myometrium M and does notcross the serosal wall SW on the real-time image display. In addition,the surgeon knows that the stops in the treatment probe are nowappropriately set to deploy the needle and tines to achieve thetreatment result shown by the virtual boundaries in FIG. 13A.

While holding the treatment probe 16 steady, the physician then advancesthe needle slide 36 (after depressing the release), as shown in FIG.14B, causing the needle 56 to extend into the fibroid F, as shown inFIG. 14A. The illustration in 14A includes a representation of thetreatment probe 16 which corresponds to the physical probe which ispresent in the patient. The remainder of FIG. 14A corresponds to theimage present on the target display 14.

After needle 56 has been fully deployed as limited by the needle stophousing 64 in the treatment probe 16, the tines 57 may be deployed byadvancing the tine slide 40 until it engages the tine stop 66, as shownin FIG. 15B. Optionally, the treatment probe 16 may be rotated about acentral axis (typically aligned with the axis of the needle 56) toconfirm the treatment and safety boundaries in all planes of view aboutthe fibroid. Display 14 will show the position of the treatment andsafety boundaries in real time relative to the target fibroid andserosa. The tines are then configured as shown in FIG. 15A, and powercan be supplied to the tines (and optionally the needle) in order toachieve treatment within the boundary depicted by the virtual treatmentboundary TB. Again, FIG. 15A mixes both the virtual image which would bepresent on the display 14 as well as the physical presence of thetreatment probe 16.

Referring now to FIG. 16A through 16D, the controller 12 can beprogrammed to display fiducials or markers on the image display 14,where the fiducials or markers represent particular locations on the“virtual” needle and/or tines. For example, as shown in FIG. 16A, marker140 may represent a position on the needle 56, for example, the locationfrom which the tines will diverge. An additional marker 142 may beprovided which represents the tip of the needle. A plurality ofadditional markers 144 may represent the tips of the tines. The use offiducials or markers 142 and 144 help the physician confirm that theactual needle and tines are deployed correctly. The physician should beable to observe the real-time images of the actual needle and tinesduring deployment, and the associated tips should move until the needletip reaches marker 142 and the tine tips hit markers 144. (oralternatively the alternative targets in FIGS. 16B-16D as describedbelow).

FIG. 16B is similar to FIG. 16A, except that the fiducials representingthe tips of the tines are depicted as arcs 146 which represent a rangeof possible positions for the distal tips of each tine. Such additionalinformation may be useful for the physician when determining bothadequacy of treatment and safety risks. As shown in FIG. 16B, each archas a radius equal to the theoretical electrode deployment length. Asshown in FIG. 16C, arcs 148 all have the same radius measured from theorigin located at the tip 142. Finally, in FIG. 16D, the arcs of FIG.16C are joined into a continuous arc which is intended to present a moreclear visual presentation for use by the physician.

As described thus far, the illustrated embodiments of the needle housinghave all included mechanisms for placing a needle stop and a tine stopfor both adjusting the virtual images of the treatment and safetyboundaries on the display screen and for subsequently positioning theactual needles and tines in the patient tissue for treatment. Analternative needle housing 202 which dispenses with the needle and tinestops is illustrated in FIGS. 17A-17C. The needle housing 202 includesboth a treatment cord 204 and a needle shaft 206, both of which aregenerally the same in structure and purpose as described for previousembodiments, and the needle housing can be secured to and removed froman imaging housing 28 as described in the previous embodiments. A needlecarriage 208 within the needle housing 202 and a tine slide 214 withinthe needle carriage 208 (FIG. 17C), in contrast, are freely positionableby the user and are not limited by stops or any other motion limitingmechanisms. Instead, the position of the needle carriage 208 is trackedby a needle carriage position sensor 210 on the bottom of the needlehousing 202, as best seen in FIG. 17A. Similarly, the tine slide 214 istracked through a position sensor 216 which is on an upper portion ofthe needle carriage 208, as best seen in FIG. 17C.

The physician or other user may virtually position the treatmentboundary and/or the safety boundary on a display screen using aninterface other than the control knob 30 as described for previousembodiments. For example, the treatment and/or safety boundaries may bepositioned on a display screen having a real time image of the uterineanatomy using a keyboard, a mouse, a roller ball, a touch screen, voiceactivation, or any other conventional interface used with computer andother displays. The virtual treatment and/or safety boundaries will beset relative to the actual position of the needle shaft 206 which can betracked by the system using the image of the shaft in tissue. After thephysician is satisfied with the placement of the virtual treatmentand/or safety boundaries, the physician can then manually advance theneedle while the system controller monitors the advancement through thesensor 210 in the needle housing 202. Through visual, audible, or othermeans, the system can alert the physician when the needle has beenadvanced by the appropriate distance. After locking the needle, the usercan then advance the tines manually while the controller monitors theirposition via the sensor 216. The system will again alert the physicianwhen the tines have been deployed by the appropriate amount within thelimits of the virtual treatment and/or safety boundaries. The system canthen alert the physician that treatment may commence.

A still further alternative embodiment of a needle housing 230 isillustrated in FIGS. 18A and 18B. The needle housing 230 again includesa treatment cord 232 and a needle shaft 234 which are generally the sameas those described for all previous embodiments. A needle carrier 236,however, differs from previous embodiments in that it is driven by adrive screw 240 which in turn is driven by a servo motor 242. The servomotor will be controlled by the system controller 12 based oninformation relating to the boundaries of the treatment region and/orsafety region, which can be produced by any of the methods discussedpreviously.

Similarly, a tine slide 244 is driven by a tine slide drive screw 246,as best seen in FIG. 18B. The tine slide drive screw, in turn, is drivenby a tine servo motor 248 which is also driven and controlled by thesystem controller. The needle carrier 236 may further comprise a needlecarrier position sensor 250 and a tine slide position sensor 252,although such position sensors are not essential since the servo motorsshould provide accurate position data regarding the needle carrier 236and the tine slide 244. The position sensors, however, are useful sincethey allow for initializing the positions and for confirming thepositions during the needle and tine deployment operations. The tineslide position sensor 252 can be connected through a flexible connectorstrip 254.

Embodiments employing servo-driven needles and tines may be combinedwith most of the previously described embodiments, including bothembodiments where the treatment and/or safety boundaries are determinedvirtually prior to needle deployment in those embodiments where thetreatment and/or safety boundaries are determined while the needlestructures are being deployed.

Referring now to FIG. 19, in certain embodiments of the presentinvention, the needle and/or tine positions may be determined based onthe ultrasound image information rather than on information from thetreatment probe configuration. As shown, an ultrasound data stream fromthe on-board imaging transducer provides both the normal image which ispresented on the display and provides the needle image and locationinformation to the system controller. The user inputs the boundarylocations to the system controller by any of the ways describedpreviously. The system controller can then calculate the treatmentand/or boundary regions and compare those to the actual boundaries whichwould be obtained based on the monitored needle/tine positions.

Referring now to FIG. 20, the systems and methods of the presentinvention can also rely on external needle tracking, such as the use ofradio frequency tags, for tracking real-time needle position in tissue.The real-time data can then be relied on by the system controller todetermine whether the needles remain within the boundaries so that bothsafe and effective treatment can be effected.

While preferred embodiments of the present invention have been shown anddescribed herein, it will be obvious to those skilled in the art thatsuch embodiments are provided by way of example only. Numerousvariations, changes, and substitutions will now occur to those skilledin the art without departing from the invention. It should be understoodthat various alternatives to the embodiments of the invention describedherein may be employed in practicing the invention. It is intended thatthe following claims define the scope of the invention and that methodsand structures within the scope of these claims and their equivalents becovered thereby.

What is claimed is:
 1. A method for deploying a needle structure intissue, said method comprising: positioning a probe having a deployableneedle structure near an anatomical feature in the tissue; providing areal time image of the tissue including the anatomical feature to betreated on a display connected to a controller; projecting a treatmentregion and a safety region on the real time image prior to deploying theneedle structure; adjusting a size and a position of a boundary of atleast one of the projected image of the treatment region and safetyregion on the real time image prior to deploying the needle structure,wherein adjusting the size and position of the projected boundarycomprises adjusting a user interface connected to the controller; anddeploying the needle structure from the probe, wherein the needlestructure is positioned relative to the probe and the tissue to providetreatment within the projected boundary after the projected boundary hasbeen adjusted.
 2. A method as in claim 1, wherein a position of theprojected boundary is adjusted by manually repositioning the proberelative to the anatomical feature.
 3. A method as in claim 1, whereinthe interface comprises a keyboard, mouse, roller ball, or touch screenwhich is connected to the controller.
 4. A method as in claim 1, whereinthe interface is on the probe.
 5. A method as in claim 4, wherein theinterface on the probe also adjusts mechanically a needle deploymentstop on the probe, wherein advancement of the needle to the needledeployment stop assures that the treatment region will be treated andthat treatment will not extend beyond the safety region.
 6. A method asin claim 5, wherein the needle structure further comprises a pluralityof tines which are advanceable from the needle in a distally divergingpattern, wherein the extent of advancement of the tines at least partlydetermines the size of the treatment region and/or the safety region. 7.A method as in claim 6, wherein the size of the projected boundary isadjusted by manually positioning a tine stop element on the probe.
 8. Amethod as in claim 7, wherein tine stop element provides a physicallimit on advancing the plurality of tines so that when the tines areadvanced to the tine stop element the tines will be located in tissuewithin the treatment region and/or safety region.
 9. A method as inclaim 1, wherein deploying the needles comprises driving a servo motorcontrolled by the controller to advance the needle structure.
 10. Amethod as in claim 6, wherein deploying the tines comprises driving aservo motor controlled by the controller to advance the tines.
 11. Amethod as in claim 1, further comprising delivering energy through theneedle structure to target tissue.
 12. A method as in claim 11, furthercomprising controlling at least one of treatment power or treatment timeto limit the extent of tissue treatment to within the treatment regionand/or safety region.
 13. A method as in claim 1, further comprisingprojecting virtual needle structure location information onto thedisplay.
 14. A method as in claim 13, wherein the virtual needlestructure location information comprises markers representing locationson the needle.
 15. A method as in claim 13, wherein the virtual needlelocation information is updated on the display as the probe stops areadjusted.
 16. A method as in claim 1, further comprising projectingactual needle structure location information onto the display.
 17. Amethod as in claim 16, wherein the actual needle structure locationinformation is derived from sensors on the probe which track needlestructure deployment.
 18. A method as in claim 16, wherein the virtualneedle location information is updated on the display as the needlestructure is deployed.
 19. A method as in claim 1, wherein adjusting thesize and position of the projected boundary is performed while the probeis being held stationary.